US11207505B2 - Balloon catheter and fluid management system thereof - Google Patents

Abstract

A balloon catheter device with a fluid management system includes a source of balloon fill media and a balloon catheter in fluid communication with the source of balloon fill media. A first conduit is provided for delivering the balloon fill media from the source to the balloon catheter for inflation of a balloon of the catheter device. A second conduit is provided for returning the balloon fill media from the balloon catheter to the source for deflating the balloon. A first pump is disposed along one of the first conduit and the second conduit for pumping the balloon fill media through the respective conduits. The fluid management system operates in three states, namely, (1) a first state in which the balloon fill media is delivered to the balloon for inflation thereof, (2) a second state in which the balloon fill media is removed from the balloon for deflation thereof; and (3) a trapped volume mode in which the balloon fill media is circulated through the balloon so as to maintain an at least substantially constant pressure in the balloon. The fluid management system is configured to maintain a pressure of the balloon between 0.2 psi and 1 psi while maintaining adequate fluid flow to cool the balloon.

Description

CROSS-REFERENCE TO RELATED APPLICATION

The present invention claims priority to U.S. patent application Ser. No. 62/443,270, filed Jan. 6, 2017, which is hereby incorporated by reference in its entirety.

BACKGROUND

This invention relates to balloon catheters and specifically to balloon catheters used to treat atrial fibrillation by creating regions of electrically non-conducting tissue in the region of the left atrium where generally the pulmonary veins join the left atrium. Prior art describes balloon catheters which can ablate tissue in the regions of the pulmonary veins and specifically balloon catheters which ablate tissue using laser energy of 980 nm or similar and also employ a endoscopes positioned inside the balloons of such catheters to view how the balloons contact the atrial tissue. Such endoscopic visualization allows for aiming of the laser energy into tissue contacting the balloon as opposed aiming the laser into areas of the balloon not in contact with atrial tissue since such latter energy delivery would be ineffective at creating lesions which block electrical conduction of the atrial tissue.

SUMMARY

The overall aims of the invention are to provide a balloon catheter system that allows for a much greater area of contact between the balloon and the atrial tissue than is achievable by prior art. Greater area of tissue contact is highly desirable since it allows for more flexibility in choosing locations to deliver laser energy. Such flexibility is desirable to avoid areas adjacent to structures which might be damaged by energy delivery such as the esophagus or the phrenic nerve. A greater area of contact also means that less time must be spent manipulating the balloon in order to achieve a balloon position where contact is adequate to allow for the delivery of the desired pattern of lesions in the region of the pulmonary vein ostium. The invention achieves the aim of increasing balloon to tissue contact area by the following means:

• • a) Providing a balloon with more compliant material properties.
  • b) Providing a system that allows the balloon to be inflated such that the pressure in the balloon is substantially lower than prior art allows.
  • c) Providing a balloon shape that achieves a more stable balloon position when the balloon is placed at the ostium of a pulmonary vein.
  • d) Providing a balloon shape that more readily conforms to the geometry of the pulmonary vein ostium.

How these means increase tissue contact with the balloon and how these means are implemented in actual practice are described in more detail below.

BRIEF DESCRIPTION OF THE DRAWING FIGURES

FIG. 1 is a schematic showing an exemplary compliant balloon in contact with a pulmonary vein ostium with balloon forces being shown;

FIG. 2 is a side view of a conventional balloon shape;

FIG. 3 is a side view of a compound taper balloon shape;

FIG. 4 is a schematic of a conventional balloon catheter device with a fluid management system;

FIG. 5 is a schematic of a balloon catheter device with a fluid management system according to a first exemplary embodiment;

FIG. 6 is a schematic of the balloon catheter device with fluid management system ofFIG. 5 shown in a trapped volume mode;

FIG. 7 is a schematic of a balloon catheter device with a fluid management system according to a second exemplary embodiment;

FIG. 8 is a schematic of a balloon catheter device with a fluid management system according to a third exemplary embodiment;

FIG. 9 is a schematic of the balloon catheter device with fluid management system ofFIG. 8 shown in a trapped volume mode;

FIG. 10 is a schematic of the balloon catheter device with fluid management system ofFIG. 9 shown in a balloon inflation mode;

FIG. 11 is a schematic of the balloon catheter device with fluid management system ofFIG. 9 shown in a balloon deflation mode; and

FIG. 12 is a schematic of the balloon catheter device with fluid management system ofFIG. 9 shown in a backup mode.

DETAILED DESCRIPTION OF CERTAIN EMBODIMENT

Physics of Balloon Contact with Tissue

FIG. 1 shows a compliant balloon100 in contact with a pulmonary vein ostium. Axial force F is applied by the physician manipulating acatheter10 in order to urge the balloon100 at the distal end of the catheter toward the pulmonary vein ostium. The balloon100 makes contact with the atria and pulmonary vein tissue and a contact area of magnitude A is created. Where the balloon100 contacts tissue there is a contact pressure P_C. If the balloon membrane is thin and flexible the balloon material itself imparts negligible mechanical forces on the tissue. Consequently, the contact pressure P_Cis essentially equal to the pressure used to inflate the balloon P_B.In equilibrium, the axial force F is equal to the projection of the contact area A in the z direction times the balloon pressure P_B.For a generally conical tapered balloon shape as shown with a cone half-angle of Θ, the area of contact is given by the equation:
A=F/P_BSin Θ  (1)

From the above equation is can be seen that operating a low balloon pressure is desirable to increase the contact area of the balloon with the tissue. There are practical limits to how much force F can be applied to the catheter shaft. That force must not exceed a force that would damage atrial tissue. There are also practical limits to the taper angle of the balloon Θ. Balloons must interface with pulmonary veins of varying sizes so it is desired that the balloons have small diameter distal ends to be able to enter the smaller veins but the balloon must also have large maximum diameter in order to prevent the balloons form entering too deeply into large veins. If too small a value of theta is selected then the difference between the distal end of the balloon and the maximum diameter will be too small to allow the balloon to interface properly with a greatest range of vein sizes.

Details of the Invention Related to the Balloon

Prior art balloons have been made of elastomeric materials such as Urethane with a durometer of 90 shore A. In use these balloons are inflated to pressures of 2 to 5 PSI. The range of pressure is used in order to adjust the maximum diameter of the balloon in order to create balloon sizes compatible with an even greater range pulmonary vein sizes than is provided for by the tapered shape of the balloon. In use prior art balloons are inflated over the range of pressure stated in order to achieve maximum diameters ranging from 25 mm to 35 mm. The balloons of the current invention employ Urethane, Silicone Rubber or Polyisoprene materials in durometers ranging from 80 Shore A to 50 Shore A. In use, these balloons100 will be inflated to pressures of 0.2 PSI to 1 PSI. These much lower pressures enable greater contact area to be achieved as described above. The lower material durometers enable the balloons to be inflated to the same range of diameters of 25 mm to 35 mm while still maintaining the lower balloon pressure of 0.2 PSI to 1 PSI desired to achieve greater tissue contact with the balloon.FIG. 2 shows one prior art balloon shape. A balloon of this shape implemented in the materials described above will achieve the aims of the present invention. In addition, it has been found that a shape as shown inFIG. 3 exhibiting a compound taper achieves even greater contact with a typical pulmonary vein ostium. Prior art balloons have tapers which range from 25 degrees to 40 degrees. The compound taper of the present invention has a distal taper Θ₁of 15 degrees to 25 degrees and a proximal taper Θ₂of 30 degrees to 55 degrees. It is desirable that the proximal and distal taper regions blend together gradually with a smooth and fair shape as shown.

Details of the Invention Related to the Fluid Management System

The balloons100 of theballoon catheters10 described here are inflated with a transparent incompressible fluid. Deuterium Oxide is the fluid of choice since it is very transparent to 980 nm laser energy generally employed. However water, saline and even compressible fluids could be employed instead. The inflation media serves to inflate the balloon and is also continuously circulated through the balloon and catheter in order prevent the balloon and other catheter components from becoming too hot during energy delivery.

FIG. 4 shows an exemplary prior art fluid management system used when the desired balloon inflation pressures range from 2 to 5 PSI. In this system, areservoir20 contains a volume ofinflation media21. Avolumetric pump22, such as a peristaltic pump, is used to circulate theinflation media21 through aballoon catheter23.Inflation media21 is fed to thepump22 from the bottom of thereservoir20. After passing through thepump22, theinflation media21 passes through a length of tubing and enters asupply lumen24 of themulti-lumen balloon catheter10. Thesupply lumen24 terminates at an opening inside aballoon26 allowinginflation media21 to enter theballoon26.Inflation media21 fills theballoon26, circulates through theballoon26 and exits theballoon26 through asecond lumen25 in the multilumen balloon catheter10. From here fluid returns to thereservoir20 via a second tube.

In this system, the balloon pressure is regulated by changing the speed of thevolumetric pump22. For a given pump speed pressure, theballoon26 will increase until equilibrium is reached where the pressure in theballoon26 is sufficient to create a return flow rate back to thereservoir20 through the second (return)lumen25 in the multi-lumen catheter and the tubing back to thereservoir20 that matches the flow rate of thevolumetric pump22. In general, the flow rates and lumen sizes are such that laminar flow exists in the flow passages when Deuterium Oxide or water is used as theinflation media21. The laminar flow regime creates a condition where the balloon pressure is directly proportional to the flow rate from thevolumetric pump22.

To deflate theballoon26, thevolumetric pump22 is run in reverse. Acheck valve27 is provided to prevent air from entering theballoon26 during balloon deflation. It should also be noted that separate pathways are used to withdrawinflation media21 from thereservoir20 and to return it to thereservoir20. In this way any air in theballoon26 or fluid pathways is expelled from the system during the initial phase wheninflation media21 is introduced into a newdry catheter10. Any air in the catheter fluid passages returns to thereservoir20 along with theinflation media21 and is dissipated as is exits the return tube shown in the figure returning drops ofinflation media21 to thereservoir20.

The prior art fluid management system is not suitable for use in the present invention where the desired balloon inflation pressures are only 0.2 PSI to 1 PSI. To achieve these low pressures with the prior art system the flow rate must be reduced to a low flow rate that is no longer adequate to cool the balloon and catheter components sufficiently. Additionally, since balloon pressure and axial force on the balloon catheter are related as shown inFIG. 1 andequation 1, balloon pressure may be transiently increased by transiently increasing axial force as unavoidably occurs during a procedure. The source of such transient increases are numerous and include patient breathing, Physician adjustments to the force on the catheter and physician fatigue. This transient increase causes the inflation media outflow to increase and allows the balloon to deflate slightly. For balloon pressures of 2 PSI to 5 PSI these transient changes in balloon pressure and balloon inflation are not significant nor noticeable but, at significantly lower pressures of 0.2 PSI to 1 PSI the effects are large enough that the balloon may deflate enough for wrinkles to appear in the balloon and for the balloon position at the pulmonary vein ostium to change. Both these conditions are undesirable. The present invention addresses these problems as described below.

FIG. 5 shows afluid management system200 according to at least one implementation of the present invention that avoids the problems detailed above. Thesystem200 includes a number of components that are illustrated inFIG. 4 and therefore, like elements are numbered alike.

In thissystem200, adiverter valve210 is added to the prior art system ofFIG. 4. Thediverter valve210 is a two-position valve. When in the position shown inFIG. 5, thediverter valve210 allows thesystem200 to function identically to the prior art system ofFIG. 4. Theballoon26 may inflated to a given pressure by adjusting thevolumetric pump speed22. Deflation is achieved by reversing thepump22 and air elimination occurs in a manner identically to the prior art system. Once theballoon26 is inflated to the desired pressure as determined by observing the endoscopic image or by observing the change in the level of inflation media in the reservoir (or by other means such as observing a fluoroscopic or echocardiographic image of the balloon residing the patient), thediverter valve210 is repositioned to the position shown inFIG. 6.

In this configuration ofFIG. 6, theinflation media21 filling thecatheter23 andballoon26 is recirculated through thecatheter10 in a closed loop fashion. In this mode, a specific volume ofinflation media21 is “trapped” in theballoon catheter23 and associated tubing. Hence, the volume ofinflation media21 filling theballoon26 will not change if the pump speed is changed or if the axial force on thecatheter23 is transiently altered. While in this mode, the pump speed may be increased to that necessary to achieve a desired level of cooling and this will have no effect on the balloon pressure or size. In actual operation with thesystem200 running as shown inFIG. 4 (Inflate/Deflate/Purge Mode), balloon inflation pressure of 0.2 PSI to 1 PSI will be achieved with pump flow rates of 2 ml/minute to 10 ml/minute. The minimum flow rate necessary to achieve the required level of cooling is 10 ml/minute. To achieve this level of flow during laser energy delivery, first theballoon26 is inflated to the desired pressure or volume, trapped volume mode is then entered and then the pump speed is increased to at least 10 ml/minute.

It is worth noting that when thesystem200 is in trapped volume mode, thevolumetric pump22 may create less than atmospheric pressure at the pump intake (this is the left side of the pump as it is shown inFIGS. 5 and 6.) Generally, the faster thevolumetric pump22 runs, the lower the pressure at the intake side of the pump. The pump speed must not be increased beyond that speed which will create an intake pressure lower than the vapor pressure of the inflation media or create a pressure so low that that pressure will cause gas dissolved in the inflation media to come out of solution and form gas bubbles. Limiting the pump intake pressure to no lower than 5 PSI below atmospheric pressure will prevent dissolved gas outgassing or inflation media vaporization. Pump speeds of 50 ml/minute or less will achieve the desired limit on intake vacuum. This flow rate is more than adequate to provide adequate cooling for the catheter.

FIG. 7 shows an additional method of balloon inflationmedia management system300. Here thediverter valve210 has been replaced by a secondvolumetric pump310. In thissystem300, all the necessary functions of the inflationmedia management system300 are accomplished by control of the speed and direction of the first and secondvolumetric pumps22,310. To initially inflate theballoon26, thefirst pump22 runs in the direction shown inFIG. 7. To purge air form thesystem300, both thefirst pump22 and thesecond pump310 run at the same speed after theballoon23 has been initially inflated. To increase the balloon size, thefirst pump22 is run faster than thesecond pump310 for a brief interval. To decrease the balloon size, thesecond pump310 is run faster than thefirst pump22 for a brief interval. Once any desired balloon size is achieved, the first andsecond pumps22,310 can be run at the same speed to maintain the balloon size at any desired flow rate. This mode is identical to the “trapped volume mode” described above for the system inFIGS. 5 and 6. To rapidly deflate theballoon26, the first andsecond pumps22,310 are run in the reverse direction from that shown inFIG. 7. Ideally, the twopumps22,310 are connected to a control system so that the coordinated actions of the twopumps22,310 are achieved by touching control buttons that create the necessary pump actions for balloon inflation, purging, size increase, size decrease, cooling during ablation at constant balloon size and deflation.

FIG. 8 shows anothersystem400 with similar operation to the system shown inFIGS. 5 and 6 and therefore like numbers are used for like elements. For thesystem400 inFIG. 8, the diverter valve has been replaced by two three-way valves, namely a first three-way valve410 and a second three-way valve420. Such valves have connections for three different flow passages and, depending on the position of thevalve410,420, allow any two passages to be interconnected with the third passage being dead-ended. In addition, a third two-way valve430 (or open-closed valve) has been added whose function is described below.

FIG. 8 shows thesystem400 with thevalves410,420,430 positioned so thesystem400 is in the Inflate/Deflate/Purge Mode. The system as shown will operate identically to the system shown inFIG. 4. The degree of balloon inflation is determined by the pump speed. Running the pump in reverse will deflate theballoon26. With the pump running in the forward direction, air is easily purged from the system. Changing the positions of the three-way valves410,420 to that shown inFIG. 9 switches thesystem400 to trapped volume mode with identical operation to thesystem400 shown inFIG. 6. Here the balloon inflation state is independent of pump speed and transient changes to the axial force on thecatheter23 will not alter the inflation state of theballoon26. Further changing the position of the uppermost three-way valve410 to that shown inFIG. 10 allows the balloon size to be increased. Once the desired increased size is achieved the uppermost three-way valve410 is positioned back to the position shown inFIG. 9. Finally, if the two-way valve430 is opened as shown inFIG. 11, the balloon size will decrease.FIG. 12 shows a backup mode in which fluid flows to thecatheter23 and is retuned back to thereservoir20. The two-way valve430 is closed, while the three-way valve410 is open and the three-way valve420 is also open.

Other valve and pump schemes are possible to achieve the functions described above. For example, the valving functions can easily be achieved by using readily available solenoid operated pinch valve actuators which serve to punch closed standard PVC medical tubing.

With all the described inflation media management systems, the valves and pumps are ideally connected to an automatic control system that allows the desired operations (Purge, Inflate, Increase Balloon Size, Decrease Balloon Size, Deflate and Trapped Volume Mode) to be easily achieved with the press or touch of a button. Ideally such a control system can be fitted with a sterile transparent drape so the fluid control operations can be performed by an operator who scrubbed in and operating the catheter at the same time. However, the systems described are perfectly useful with the valves and pumps being operated individually and manually.

Notably, the figures and examples above are not meant to limit the scope of the present invention to a single embodiment, as other embodiments are possible by way of interchange of some or all of the described or illustrated elements. Moreover, where certain elements of the present invention can be partially or fully implemented using known components, only those portions of such known components that are necessary for an understanding of the present invention are described, and detailed descriptions of other portions of such known components are omitted so as not to obscure the invention. In the present specification, an embodiment showing a singular component should not necessarily be limited to other embodiments including a plurality of the same component, and vice-versa, unless explicitly stated otherwise herein. Moreover, applicants do not intend for any term in the specification or claims to be ascribed an uncommon or special meaning unless explicitly set forth as such. Further, the present invention encompasses present and future known equivalents to the known components referred to herein by way of illustration.

The foregoing description of the specific embodiments will so fully reveal the general nature of the invention that others can, by applying knowledge within the skill of the relevant art(s) (including the contents of the documents cited and incorporated by reference herein), readily modify and/or adapt for various applications such specific embodiments, without undue experimentation, without departing from the general concept of the present invention. Such adaptations and modifications are therefore intended to be within the meaning and range of equivalents of the disclosed embodiments, based on the teaching and guidance presented herein. It is to be understood that the phraseology or terminology herein is for the purpose of description and not of limitation, such that the terminology or phraseology of the present specification is to be interpreted by the skilled artisan in light of the teachings and guidance presented herein, in combination with the knowledge of one skilled in the relevant art(s).

While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example, and not limitation. It would be apparent to one skilled in the relevant art(s) that various changes in form and detail could be made therein without departing from the spirit and scope of the invention. Thus, the present invention should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents.

Claims (12)

What is claimed is:

1. A balloon catheter system comprising:

a catheter body having a distal end; and

a balloon coupled to the distal end, the balloon being inflated to and maintained at a specific inflation pressure between about 0.2 psi and about 1 psi for seating against a pulmonary vein ostium.

2. The balloon catheter system ofclaim 1, wherein the balloon is formed of a material selected from the group consisting of urethane, silicone rubber and polyisoprene and has a durometer between about 80 Shore A and about 50 Shore A.

3. A balloon catheter system comprising:

a balloon catheter including a catheter body and an inflatable balloon coupled to one end thereof; and

a fluid management system for controllably inflating and deflating the balloon, the fluid management system including a reservoir for storing balloon fill media, a first conduit connected between the reservoir and the balloon for delivering the balloon fill media, a second conduit connected between the balloon and the reservoir for returning the balloon fill media from the balloon to the reservoir, a first pump disposed along the first conduit between the reservoir and the balloon, wherein a third conduit is in fluid communication between the first and second conduits, wherein a first three-way valve is disposed along the first conduit between the first pump and the reservoir resulting in the first pump being disposed between the first three-way valve and the balloon and a second three-way valve is disposed along the second conduit and a check valve is disposed along the second conduit between the second three-way valve and the reservoir, wherein one end of the third conduit is connected to the first conduit at a location between the first pump and the balloon and an opposite end of the third conduit being connected to the second conduit at a location between the check valve and the second three-way valve, wherein a two-way valve is disposed along the third conduit, wherein the first and second three-way valves and the two-way valve are positionable in: (1) a first position that corresponds to an inflate/deflate/purge mode in which the first three-way valve is open, the second three-way valve is open and the two-way valve is closed, (2) a closed circuit mode in which an inflation level of the balloon is maintained, wherein the first three-way valve is closed, the second three-way valve is closed and the two-way valve is open to allow the balloon fill media to circulate through the balloon by flowing from the first conduit through the balloon to the second conduit, (3) an increase balloon size mode in which the first three-way valve is open, the second three-way valve is closed and the two-way valve is closed, and (4) a decrease balloon size mode in which the first three-way valve is closed, the second three-way valve is closed and the two-way valve is open.

4. The balloon catheter device ofclaim 3, wherein in the first position, an operating speed of the first pump determines inflation level in the inflatable balloon and operation of the first pump in a first direction causes inflation of the inflatable balloon and operation of the first pump in an opposite second direction causes deflation of the inflatable balloon.

5. A balloon catheter device with a fluid management system comprising:

a source of balloon fill media;

a balloon catheter in fluid communication with the source of balloon fill media;

a first conduit for delivering the balloon fill media from the source to the balloon catheter for inflation of a balloon of the catheter device;

a second conduit for returning the balloon fill media from the balloon catheter to the source for deflating the balloon;

a first pump disposed along one of the first conduit and the second conduit for pumping the balloon fill media; and

wherein the fluid management system operates in three states, namely, (1) a first state in which the balloon fill media is delivered to the balloon for inflation thereof, (2) a second state in which the balloon fill media is removed from the balloon for deflation thereof; and (3) a trapped volume mode in which the balloon fill media is circulated through the balloon so as to maintain an at least substantially constant pressure in the balloon by creating a closed recirculation loop in which the source of balloon fill media is isolated and the first pump circulates the balloon fill media in the closed recirculation loop without drawing balloon fill media from the source of balloon fill media and without returning the balloon fill media back to the source of balloon fill media by causing the balloon fill media to flow along a section of the first conduit into the balloon and then exiting the balloon through the second conduit and flowing through a branch conduit from the second conduit to the first conduit at a location upstream of the first pump, wherein a plurality of valves located along the first conduit and the second conduit are in trapped volume mode settings to define the closed recirculation loop;

wherein the fluid management system is configured to maintain a pressure of the balloon between 0.2 psi and 1 psi.

6. The balloon catheter device ofclaim 5, further including a check valve that is disposed in the second conduit and a third conduit that extends between the first conduit and the second conduit.

7. The balloon catheter device ofclaim 6, wherein the fluid management system comprises a plurality of valves that are disposed along the first conduit and the second conduit, wherein in the trapped volume mode, the balloon fill media is recirculated through the balloon and the third conduit is in an offline position.

8. The balloon catheter device ofclaim 7, wherein the plurality of valves comprises a first three-way valve disposed along the first conduit upstream of the first pump and a second three-way valve disposed along the second conduit and a two-way valve that is within the third conduit that extends between the first conduit and the second conduit and is connected to the first conduit downstream of the first three-way valve and the first pump and is attached to the second conduit downstream of the second three-way valve.

9. The balloon catheter device ofclaim 8, wherein in the first state, which is an inflate the balloon state, the first three-way valve is open, the second three-way valve is closed, and the second two-way valve is closed, wherein in the second state, the first three-way valve is closed, the second three-way valve is closed and the two-way valve is open and wherein the trapped volume mode, the first three-way valve is closed, the second three-way valve is closed and the two-valve closed causing the balloon fill media to flow between the first three-way valve and the second three-way valve.

10. The balloon catheter device ofclaim 8, wherein the third conduit is connected to the first conduit between the first pump and the catheter and is connected to the second conduit between the check valve and the second three-way valve.

11. The balloon catheter ofclaim 5, wherein the branch conduit extends between and is in fluid communication with the first three-way valve and the second three-way valve such that in the trapped volume mode, the balloon fill media flows through the second three-way valve into the branch conduit to the first three-way valve and then to the first conduit.

12. A balloon catheter device with a fluid management system comprising:

a source of balloon fill media;

a balloon catheter in fluid communication with the source of balloon fill media;

a first conduit for delivering the balloon fill media from the source to the balloon catheter for inflation of a balloon of the catheter device;

a second conduit for returning the balloon fill media from the balloon catheter to the source for deflating the balloon; and

a first pump disposed along one of the first conduit and the second conduit for pumping the balloon fill media;

wherein the fluid management system operates in three states, namely, (1) a first state in which the balloon fill media is delivered to the balloon for inflation thereof, (2) a second state in which the balloon fill media is removed from the balloon for deflation thereof; and (3) a trapped volume mode in which the balloon fill media is circulated through the balloon so as to maintain an at least substantially constant pressure in the balloon by creating a closed recirculation loop in which the source of balloon fill media is isolated and the first pump circulates the balloon fill media in the closed recirculation loop without drawing balloon fill media from the source of balloon fill media and without returning the balloon fill media back to the source of balloon fill media by causing the balloon fill media to flow along a section of the first conduit into the balloon and then exiting the balloon through the second conduit and flowing through a branch conduit from the second conduit to the first conduit at a location upstream of the first pump, wherein a plurality of valves located along the first conduit and the second conduit are in trapped volume mode settings to define the closed recirculation loop.

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